Cohort study into the neural correlates of postoperative delirium: … · 2020-06-24 · Delirium...
Transcript of Cohort study into the neural correlates of postoperative delirium: … · 2020-06-24 · Delirium...
British Journal of Anaesthesia, xxx (xxx): xxx (xxxx)
doi: 10.1016/j.bja.2020.02.027
Advance Access Publication Date: xxx
Clinical Investigation
C L I N I C A L I N V E S T I G A T I O N
Cohort study into the neural correlates of postoperative delirium:the role of connectivity and slow-wave activity
Sean Tanabe1, Rosaleena Mohanty1,2, Heidi Lindroth1,3, Cameron Casey1, Tyler Ballweg1,
Zahra Farahbakhsh1, Bryan Krause1, Vivek Prabhakaran2, Matthew I. Banks1 and
Robert D. Sanders1,4,5,*
1Department of Anesthesiology, University of Wisconsin, Madison, WI, USA, 2Department of Radiology, University of
Wisconsin, Madison, WI, USA, 3Center for Health Innovation and Implementation Science, Center for Aging Research,
Division of Pulmonary and Critical Care Medicine, Regenstrief Institute, Indiana University School of Medicine,
Indianapolis, IN, USA, 4University of Sydney, Australia and 5Department of Anaesthetics, Royal Prince Alfred Hospital,
Australia
*Corresponding author. E-mail: [email protected]
Abstract
Background: Delirium frequently affects older patients, increasing morbidity and mortality; however, the pathogenesis is
poorly understood. Herein, we tested the cognitive disintegration model, which proposes that a breakdown in fronto-
parietal connectivity, provoked by increased slow-wave activity (SWA), causes delirium.
Methods: We recruited 70 surgical patients to have preoperative and postoperative cognitive testing, EEG, blood bio-
markers, and preoperative MRI. To provide evidence for causality, any putative mechanism had to differentiate on the
diagnosis of delirium; change proportionally to delirium severity; and correlate with a known precipitant for delirium,
inflammation. Analyses were adjusted for multiple corrections (MCs) where appropriate.
Results: In the preoperative period, subjects who subsequently incurred postoperative delirium had higher alpha power,
increased alpha band connectivity (MC P<0.05), but impaired structural connectivity (increased radial diffusivity; MC
P<0.05) on diffusion tensor imaging. These connectivity effects were correlated (r2¼0.491; P¼0.0012). Postoperatively,
local SWA over frontal cortex was insufficient to cause delirium. Rather, delirium was associated with increased SWA
involving occipitoparietal and frontal cortex, with an accompanying breakdown in functional connectivity. Changes in
connectivity correlated with SWA (r2¼0.257; P<0.0001), delirium severity rating (r2¼0.195; P<0.001), interleukin 10
(r2¼0.152; P¼0.008), and monocyte chemoattractant protein 1 (r2¼0.253; P<0.001).Conclusions: Whilst frontal SWA occurs in all postoperative patients, delirium results when SWA progresses to involve
posterior brain regions, with an associated reduction in connectivity in most subjects. Modifying SWA and connectivity
may offer a novel therapeutic approach for delirium.
Clinical trial registration: NCT03124303, NCT02926417
Keywords: cognitive dysfunction; connectivity; delirium; electroencephalogram; inflammation; mechanism; post-
operative; slow wave activity; surgery
Received: 4 November 2019; Accepted: 28 February 2020
© 2020 British Journal of Anaesthesia. Published by Elsevier Ltd. All rights reserved.
For Permissions, please email: [email protected]
1
Editor’s key points
� Electroencephalographic slow-wave activity has previ-
ously been associated with delirium.
� We found local SWA in patients without delirium but
global SWA in patients with delirium.
� A distinguishing feature of postoperative delirium in
most patients was a decrease in correlates of fronto-
parietal connectivity.
� Decreased preoperative structural rather than func-
tional connectivity was predictive of postoperative
delirium.
2 - Tanabe et al.
Delirium is a sudden onset of confusion that frequently affects
older patients.1 It is associated with increased morbidity,
mortality, loss of functional independence, and worsening
quality of life, and may herald the onset of cognitive decline
and dementia.1,2 It is estimated to cost $160 billion per annum
in the USA.3 The pathogenesis of delirium remains obscure;
whilst several theories have been proposed,4e7 no therapies
have been forthcoming. We proposed a cognitive disintegra-
tion model,7 whereby the severe cognitive symptoms of
delirium are related to breakdown in connectivity driven by
increased EEG slow-wave activity (SWA) in key frontoparietal
cognitive networks. Inspired by the basic tenets of cognitive
frameworks, such as integrated information theory8 and pre-
dictive coding,9 we surmised that cognition requires the inte-
gration of information from functionally specialised brain
regions to form a coherent view of self and the environment.
Delirium is characterised by fragmented perceptions and
disjointed interactions with the environment, consistent with
disintegration of certain cognitive processes. Preliminary evi-
dence for this model, based on reductions in connectivity
during delirium, has been provided by Numan and col-
leagues10 and van Dellen and colleagues.11 However, the case-
control design used does not exclude premorbid differences
between the groups. We hypothesised that pre-existing de-
creases in connectivity would predispose to delirium.7 Thus,
we collected EEG data preoperatively, before delirium
occurred. The electrophysiological hallmark of delirium is
cortical SWA. Cortical SWA is a characteristic of both deep
non-rapid eye movement sleep12 and anaesthesia.13 In both of
these states, it is associated with reduced connectivity. Hence,
it is plausible that delirium-associated SWA may lead to im-
pairments in connectivity.
As there is presently no way of reversing delirium to
establish causality, we used the Bradford Hill criteria for
causation to support the importance of the mechanisms un-
covered. Hence, we sought a strong association, with specific
changes in the delirious population that changed contempora-
neously with delirium and with a biological gradient. To achieve
these criteria, the change with transition to delirium must
differ from non-delirious subjects and should also change
proportionately to delirium symptom severity (henceforth,
delirium severity). These criteria also impose a relatively
stringent statistical threshold: requiring a test to be significant
for both delirium incidence and severity would exclude
spurious results at a threshold equivalent to 0.052. Further-
more, to provide biological plausibility, we hypothesised that
relevant effects should also correlate with inflammation, a
probable precipitant of delirium. To identify relevant markers
of systemic inflammation, we identified plasma cytokines that
changed with both delirium incidence and severity.
Whilst multiple studies have shown that delirium is asso-
ciated with diffuse slowing in the EEG,14 they typically have
not accounted for pre-delirium status or within- and across-
subject differences. Nor have they looked for Bradford Hill
criteria of causation nor related findings to severity or
inflammation. Herein, we took advantage of major elective
surgery, where the precipitating event for delirium is pre-
dictable in time. We tested our hypothesis that, when SWA
progressed to involve frontoparietal brain regions, the asso-
ciated breakdown in connectivity would precipitate delirium.7
Methods
The data are derived from two ongoing perioperative cohort
studies registeredwith https://clinicaltrials.gov/(Interventions
for Postoperative Delirium: Biomarker-3 (IPOD-B3),
NCT03124303, and Interventions for Postoperative Delirium:
Biomarker-2 (IPOD-B2), NCT02926417) and approved by the
University of WisconsineMadison Institutional Review Board
(#2015-0374; 2015-0960). EEG data were collected from 72 pa-
tients before and after surgery between 2015 and 2019. Two
subjects’ data were excluded because of poor impedance
contaminating the entire recording. After exclusion of these
two subjects, all available EEG data (in subjects with paired
preoperative and postoperative EEG) collected until 70 subjects
were recruitedwere used in the analyses (Fig. 1). Eight subjects
were recruited only to IPOD-B2 and 62 to IPOD-B3. Sensitivity
analyses, conducted only on subjects recruited to IPOD-B3,
found similar results. IPOD-B2 is a small ongoing cohort
study of adult subjects undergoing thoracic aortic aneurysm
repair (open or endovascular; Supplementary Table 1). IPOD-
B3 is a larger ongoing cohort of adult patients (>65 yr old)
undergoing major surgery (Supplementary Table 1).
Cohort sample size
A priori power analysis suggested that a minimum of 59 sub-
jects would be required to show EEG differences in delirium.
Prior data suggested an effect size for a ‘between-subject’
analysis of a three-fold increase in SWA11 in delirium. Based
on the variance in SWA from van Dellen and colleagues,11
power analysis suggests that 12 delirious subjects, compared
with 47 controls, will provide 99% power for an uncorrected
a<0.001 to detect SWA differences assuming a 20% delirium
incidence. Calculation of SWA differences required paired EEG
samples for preoperative and postoperative data from which
we could calculate the change in the delirious subjects and
compare with the change in the non-delirious subjects.
Delirium diagnosis
The 70 subjects were grouped depending on postoperative
confusion assessment method diagnoses of delirium (confu-
sion assessment method [CAM]þ/e15,16 or CAM-ICUþ/e if
ventilated17) status at the time of the EEG recording as delir-
ious or not.15 The delirium group contained 22 subjects and the
non-delirium group contained 48 subjects. Delirium severity
was scored using the Delirium Rating of Severity-98 (DRS).18
Weekly delirium review meetings were held to ensure con-
sistency of scoring during the data collection period.
Fig 1. Study design and Strengthening the Reporting of Observational Studies in Epidemiology (STROBE) diagram. (a) Study design.
Delirium severity (DRS) is collected during both preoperative and postoperative delirium assessment. (b) STROBE diagram. Data are from
IPOD-B2 and IPOD-B3 ongoing perioperative cohort studies. DRS, Delirium Rating of Severity-98; DTI, diffusion tensor imaging; IPOD-B2,
Interventions for Postoperative Delirium: Biomarker-2; IPOD-B3, Interventions for Postoperative Delirium: Biomarker-3.
Neural correlates of delirium - 3
EEG recording and preprocessing
EEG data were collected using high-density EEG with 256 chan-
nels (Electrical Geodesics, Inc., Eugene, OR, USA) using a sam-
pling frequency of 250 Hz (five subjectswere recorded at 500 Hz;
these were down sampled to 250 Hz). Data were collected pre-
operativelywithamedianof5daysbeforesurgery (inter-quartile
range [IQR]: 1e7 days) and postoperatively with amedian of the
first postoperative day (IQR: 1e1 day). For each subject and
condition, 15 min of eyes-closed resting-state data were
collected. Inthreesubjects, eyes-opendata foraminimumof90s
were collected allowing comparison of eyes open and closed.
These data were filtered from 0.1 to 50 Hz using Hamming
windowed-sinc FIR filter. Channels and data segments con-
taining artifact were visually inspected and removed. To
remove artifact of eye movement and muscle movement, we
applied independent component analysis in EEGLAB. Before
analysis, the removed channels were interpolated, and then
the signals were average-referenced.
4 - Tanabe et al.
Spectral power
The data were estimated for power spectral density with
Welch’s method into delta (0.5e4 Hz), theta (4e6 Hz), alpha
(6e12 Hz), beta (12e28 Hz), and gamma (28e40 Hz). The power
spectral density was log10 transformed to normalise the dis-
tribution. Slow-wave activity was post hoc defined as 0.5e6 Hz
similar to prior definitions.19
Phase lag index
To measure the functional connectivity between channel sig-
nals, the debiased weighted phase lag index (PLI) in the
FieldTrip toolbox (maintained by the Donders Institute for
Brain, Cognition, and Behaviour which is part of Radboud
University in Nijmegen, the Netherlands) was used.20 Phase
lag index alone estimates the degree to which the two time-
series leads and lags by indexing their phase differences.
However, PLI is sensitive to signal synchronisations because of
volume conduction. By weighting the phases across cross-
spectrum time series, PLI is able to mitigate the sensitivity to
volume conduction.20 Debiasedweighted PLI further estimates
the squared weighted PLI to normalise the positive bias.
Between all 256 channels, in a pairwise manner, we
calculate debiased PLI using 2 s window length and 25%
overlap. To probe changes associated with detectable SWA in
both the delirious and non-delirious groups, we divided the
256 scalp electrodes in 25 squares (Supplementary Fig. 1). The
PLI between these ‘squares’ were averaged, producing
pairwise-squared PLI. We focused on PLI involving the midline
frontal square centred on the Fz electrode, which showed
increased SWA in both delirious and non-delirious subjects.
However, we also conducted pairwise analyses across con-
nections and correlated these changes in connectivity with
delirium severity. These analyses were corrected by false
discovery rate (FDR) methods. We also plot a PLI spectrum by
using the cross-spectra produced from multi-taper frequency
transformation (see Supplementary data for methods).
EEG statistical analysis
To test for topographical differences or correlations, two-
tailed statistical non-parametric mapping (SNPM) threshold-
free cluster enhancement was used.21 Wilcoxon rank-sum
test, Wilcoxon signed-rank test, and Pearson correlation
were used for non-topographical tests where appropriate. To
test for differences amongst groups (across delirium status
and pre-/postoperation), we used linear mixed-effects models,
testing the interaction of delirium status and time point (pre vs
post) for each frequency band. Test statistics and P-values
were calculated using Type III Wald F-tests with
KenwardeRoger degrees of freedom.
Topographical PLI analyses use parametric Pearson corre-
lation on each PLI connection. These analyses are sensitive to
outlier influence, as parametric tests assume a homogeneous
variance. Therefore, for each PLI connectivity, we excluded
outlier subjects whose Cook’s distance is above 4*(mean of
Cook’s distance).22 Excluding subjects with large Cook’s dis-
tances resulted in substantial changes to the regressionmodel
estimation. As each PLI connectivity topoplot has a different
regression model, there will be a different number of subjects
excluded for each connection. Because of this, analyses mak-
ing use of Cook’s distance will indicate sample size as a range
(e.g. n¼70 [64e69, after outlier exclusion]). The PLI analyses
were corrected by FDR methods.
Blood biomarkers
We also collected blood samples for biomarker analyses
immediately before and after the resting-state EEG. Plasma
samples were collected in ethylenediamine tetra-acetic acid
(EDTA)-containing tubes preoperatively and stored at e80�C.
Cytokine analysis
A multiplex assay was conducted at Eve Technologies (Mon-
treal, Canada) for plasma samples that were paired with EEG
collection. The cytokines measured were interleukin (IL) 1 (IL-
1) beta, IL-1 receptor antagonist, IL-2, IL-4, IL-6, IL-8, IL-10, IL-
12, monocyte chemoattractant protein 1 (MCP-1), and tumour
necrosis factor-alpha. For the cytokine analysis only, subjects
were excluded if they had no blood drawn around the time of
the EEG recording.
Diffusion tensor imaging methods
A post hoc decisionwasmade during the analysis of EEG data to
investigate preoperative structural connectivity (diffusion
tensor imaging [DTI]) in patients with EEG to investigate an
unexpected findingwith preoperative frontal EEG connectivity.
All availableDTI data in the cohort are reported. Of the patients
recruited to IPOD-B3, 75 patients consented to preoperative
imaging (there is no imaging collected in IPOD-B2). Six of the
DTI scans were discarded because of motion artifact. Preoper-
ative DTI scans were available from 68 patients (17 delirious)
after quality control and preprocessing. Thirty-six subjects had
preoperative imaging and EEG.MRI datawere collected on 3.0 T
whole-body scanner (General Electric Medical Systems, Wau-
kesha, WI, USA) with an eight-channel head coil. Diffusion
tensor imaging datawere acquiredwith the followingdiffusion
parameters: single-shot echo planar imaging, repetition
time¼9000ms, echo time¼66.2ms, single average (NEX) 1, field
of view 256�256 mm2, voxel size 1�1�2 mm3, 75 axial slices
with no gap between slices, flip angle 90�, 56 gradient encoded
directions, and b-values of 0 and 1000 s mm�2.
The raw DTI were checked manually for quality control,
and each remaining scan was corrected for head motion and
eddy-current distortionwith the eddy23 tool and skull stripping
and removal of non-tissue components in FSL.24 The diffusion
tensor model, based on the least-squares fit, was applied using
FDT’s dtifit providing data on fractional anisotropy (FA), mean
diffusivity (MD), axial diffusivity (AD), and radial diffusivity
(RD). Non-linear registration was conducted using Advanced
Normalization Tools (ANTs is maintained by the Penn Image
Computing and Science Lab which is operated out of the
University of Pennsylvania in Philadelphia, PA, USA)25 to a
standard template based on the publicly available Mayo Clinic
Adult Lifespan Template atlas.26
Prior data emphasised RD,27 and hence, we pursued that as
our primary DTI metric, although convergent results were
obtained with MD. Voxel-wise skeletonised white matter tract
maps were obtained for each DTI metric with tract-based
spatial statistics (TBSS),28 applied to AD, MD, and RD, and
were used to perform cross-subject statistical analyses. Voxel-
wise statistical approach (randomise tool21 with threshold-free
cluster enhancement) was adopted to study the association
between the preprocessed and TBSS-based white matter
Fig 2. Delirium occurs with increased global slow-wave activity and loss of posterior high-frequency activity. (a) Representative EEG signals
from two electrodes, one frontal (Fz) and one posterior/occipital (Oz), collected preoperatively (Preop/Pre) and postoperatively (Post). (b)
Group-level spectral analysis comparing patients preoperatively and postoperatively for patients who do (D), or do not (ND), incur delirium
(P<0.05 [black squares], linear mixed-effects model across delirium status and operative phase). Spectra range from 0.5 to 40 Hz, statistics
were completed for frequency bands; d 0.5e4 Hz, q 4e6 Hz, a 6e12 Hz, b 12e28 Hz, g 28e40 Hz. The alpha band range (a), 6e12 Hz, was
chosen by inspecting the peak in the mean spectra amongst all subjects. Topological spectral power of the preoperative and postoperative
states for patients who do not incur delirium (c) or do incur delirium (d) across each power band. The third row shows the post-
operative>preoperative contrast t-maps, corrected with threshold-free cluster enhancement (TFCE), with overlaid electrodes showing
significant differences (statistical non-parametric mapping [SNPM] paired; corrected TFCE P<0.05 [white dots]). (e) Spectral analysis for the
transition in state (postoperatively-preoperatively) for subjects who incur delirium or do not (P<0.05 [black squares] after FDR correction
with two-sided rank-sum test) for electrodes Fz and Oz. Grey square: uncorrected P<0.05. (f) Topological contrasts of the transition to the
non-delirious vs delirious state (first two rows). Third row shows the TFCE t-map of two groups contrast with significant electrodes
overlaid (SNPM unpaired; TFCE corrected P<0.05 t-map). For all statistics, nND¼48 and nD¼22. PSD, power spectral density.
Neural correlates of delirium - 5
Fig 3. Posterior slow-wave activity (SWA) is associated with (a) delirium severity and (b, c) systemic inflammation. Each column represents
the correlation of change in power (postoperatively-preoperatively) with an outcome either Delirium Rating of Severity-98 (DRS), inter-
leukin (IL)-10, or monocyte chemoattractant protein 1 (MCP-1). Top row shows correlation with transition in spectral power across fre-
quencies from occipital electrode (Oz). Spectra range from 0.5 to 40 Hz; statistics done on frequency bands; d 0.5e4 Hz, q 4e6 Hz, a 6e12 Hz,
b 12e28 Hz, and g 28e40 Hz. Black square: P<0.05 after false discovery rate correction. Grey square: P<0.05 uncorrected. Middle row shows
topological correlation with the increase in SWA (0.5e6 Hz; statistical non-parametric mapping correlation; corrected threshold-free
cluster enhancement P<0.05 [white dots show statistically significant electrodes]). Bottom row shows correlation with transition in
SWA from occipital electrode Oz. DRS n¼70; IL-8 n¼47; IL-10 n¼46; MCP-1 n¼47.
6 - Tanabe et al.
skeletonised maps and delirium incidence, and severity on a
group level (using 10 000 permutations). Voxel-wise statistical
significance inferences were drawn by controlling the family-
wise error (FWE) rate at a 0.05 threshold. Detailed descriptions
of the DTI methods are available in the Supplementary
material.
Fig 4. Delirium is associated with decreased connectivity (debiased weighted phase lag index [PLI]). (a) PLI spectral analysis comparing
patients preoperatively (pre) and postoperatively (post) for patients who do (D), or do not (ND), incur delirium (P<0.05 [black squares]).
Statistical analysis using a linear mixed-effects model across delirium states and pre-/postoperation is reported (nND¼48 and nD¼22).
Spectra range from 0.5 to 40 Hz; statistics done on frequency bands; d 0.5e4 Hz, q 4e6 Hz, a 6e12 Hz, b 12e28 Hz, and g 28e40 Hz. (b)
Topologically PLI of preoperative and postoperative states for patients who do not, or do, incur delirium. PLI with a frontal square group of
electrodes is displayed and corrected. Bottom row shows postoperative>preoperative contrast (P<0.05 [line displayed if significant] after
false discovery rate (FDR) correction with two-sided Wilcoxon signed-rank test). Right column shows contrast between patients who do,
and do not, incur delirium, delirium>no delirium (P<0.05 after FDR correction with two-sided Wilcoxon rank-sum test; nND¼48 and nD¼22).
(c) Topological plots of the change in connectivity with transition to the non-delirious vs delirious state. Right, topoplot shows threshold-
free cluster enhancement t-map of two groups contrast (P<0.05 after FDR correction with two-sided Wilcoxon rank-sum test; nND¼48 and
nD¼22). (d) Correlation of the postoperativeepreoperative difference in PLI with changes in Delirium Rating of Severity-98 (DRS), inter-
leukin (IL)-10, monocyte chemoattractant protein 1 (MCP-1), and slow-wave activity (SWA). Left column shows r2 map (P<0.05 after FDR
correction; DRS n¼70 [64e69, after outlier exclusion], IL-10 n¼46 [42e45], MCP-1 n¼47 [42e46], and SWA n¼70 [63e68]). Right columns show
correlations with PLI of frontal square connecting to square below.
Neural correlates of delirium - 7
Fig 5. Preoperative connectivity is increased before delirium and inversely correlates with structural connectivity. (a) Preoperative radial
diffusivity (RD) contrast for patients who do not incur delirium (ND) and do incur delirium (D) (general linear model with covariate
ageþgender; P<0.05 family-wise error corrected; nND¼51 and nD¼17). Significant effects of RD (red) are overlaid on whole brain white
matter tract (green). The right box plot shows mean RD contrast across significant voxels detected with multiple comparison correction
between the groups (P<0.05 corrected; two-sided Wilcoxon rank-sum test). (b) Correlation of preoperative RD with peak postoperative
delirium severity (general linear model with covariate ageþgender; P<0.05 FWE corrected; n¼68). (c) Correlation of preoperative (preop)
topological alpha phase lag index (PLI) and mean RD across significant voxels (P<0.05 after false discovery rate correction; n¼36 [33e36
after outlier exclusion]). Left, topoplot shows r2 map for the PLI of frontal square is displayed and corrected. Right plot shows mean RD
correlation with PLI of frontal square connecting to parietal square. DRS, Delirium Rating of Severity-98.
8 - Tanabe et al.
Neural correlates of delirium - 9
Results
Figure 1 shows the Strengthening the Reporting of Observa-
tional Studies in Epidemiology (STROBE) diagram and data
collection strategy. Cohort characteristics are described in
Supplementary Table 2. The median postoperative DRS was 9.
Postoperative delirium occurred in 31% of patients, whose
median DRS was 17. Delirious patients had similar age and sex
to patients who did not become delirious, but they underwent
operations with higher surgical severity (Wilcoxon rank-sum
test; P<0.001; Supplementary Table 2).
EEG power spectral analyses
Initially, we focused on the within-subject change in the EEG
that occurs from preoperative to postoperative phases of care.
This showed obvious slowing on transition to the delirious
state (Fig. 2a). For quantitative analysis, the EEG was initially
segmented into different power bands, delta (0.5e4 Hz), theta
(4e6 Hz), alpha (6e12 Hz), beta (12e28 Hz), and gamma (28e40
Hz), based on our division of data around the alpha peak that is
evident in Fig. 2b. Our data show an increase in delta and theta
power in frontal regions in both the non-delirious (linear
mixed-effects model across delirium states and pre-/post-
operation Pdelta<0.0001 and Ptheta<0.0001; Fig. 2c) and delirious
(Pdelta<0.0001 and Ptheta<0.0001; Fig. 2d) subjects. A critical dif-
ference between patient groupswas that delta and theta power
increased in posterior regions in delirium, with a reciprocal
decrease in higher-frequency activity (Fig. 2b and d). Interest-
ingly, patients who later incurred delirium had higher frontal
alpha power preoperatively (P¼0.0338; Fig. 2b), but no change
postoperatively. In contrast, frontal alpha power increased
postoperatively in patients who did not incur delirium (Fig. 2c).
The preoperative differences between the subjects who did
not incur delirium postoperatively and those that did
emphasised the need to focus on the differences in EEG dy-
namics that occur on transition to delirium. Hence, we next
confirmed that the changes in SWA that occur on transition
from preoperative to postoperative state differed between the
groups (described in Supplementary Fig. 2). This analysis was
conducted to exclude non-specific EEG changes that may
occur postoperatively (such as small increases in frontal SWA).
In this focused analysis, increased global delta and theta po-
wer and loss of posterior high-frequency activity appeared
characteristic of delirium (Fig. 2e and f).
Comparison of eyes-open and eyes-closed powerspectra
The global increase in delta and theta power in delirious pa-
tients was surprising given that the subjects were sufficiently
wakeful to complete our cognitive assessments. To confirm
that the subjects were wakeful, we compared the power
spectra for delirious subjects recorded with eyes open and
closed (the latter being the typical state during the recordings).
Whilst only three delirious patients were captured with eyes
open (as delirious patients struggle to follow commands),
there was no difference in the power spectra between the
eyes-open and eyes-closed states, suggesting we were not
merely studying sleep (Supplementary Fig. 3).
EEG power spectra sensitivity analyses
We next confirmed that this effect was not driven by patients
requiring sedation for intubation on the ICU by performing a
sensitivity analysis, excluding these seven patients
(Supplementary Fig. 4). The results were unaffected by
excluding these seven patients. As delta and theta bands
showed similar effects across all these contrasts, henceforth
we treated them as one frequency range, SWA, as has been
done in studies of sleep deprivation.19,29
Correlations of EEG power and delirium severity
Next, we hypothesised that, as SWA increased, delirium
severity would worsen. We calculated the Pearson correlation
of power, for each frequency band, with the change in
delirium severity (DRS). For the purpose of display, we also
show the correlation coefficient in 0.1 Hz frequency bins.
Slow-wave activity showed a remarkable correlation with DRS
with specificity at <6 Hz, such that, as SWA increased,
delirium severity increased (Fig. 3a). Topographic analysis
showed that, whilst there were significant correlations of DRS
and SWA inmany electrodes across the scalp, the relationship
appeared strongest in posterior regions. Indeed, at electrode
Oz, the correlation was relatively strong (r2¼0.207; P¼0.0001).
However, there was no statistical difference between Fz and
Oz for the correlation with DRS with a Williams test; P¼0.67.
We identified a similar effect when excluding the seven pa-
tients on sedation (Supplementary Fig. 4), and confirmed that
all delirious subjects showed increases in Oz SWA
(Supplementary Fig. 5). Correlations of DRS with EEG changes
in higher frequencies were not observed, suggesting these
changes may not be causally related to the delirium state
(Supplementary Fig. 6). These data suggest that SWA is a key
feature of delirium.
Correlations of EEG power and cytokines
We looked for associations between cytokine changes and
delirium using a multiplex panel of 10 cytokines (Eve Tech-
nologies) using Bonferroni multiple comparison correction.
Consistent with prior studies,30 we identified significant asso-
ciations of simultaneous changes in MCP-1 (r2¼0.192; P¼0.002)
and IL-10 (r2¼0.200; P¼0.002), with both delirium severity (DRS;
Supplementary Fig. 7) and delirium incidence (Supplementary
Fig. 8). The other cytokines did not achieve significance on
both tests. Given the detected and plausible association with
delirium, we tested whether MCP-1 and IL-10 were also corre-
lated with SWA. Similar <6 Hz changes in posterior electrode
SWA were correlated with these two cytokines (Fig. 3c and d),
suggesting that systemic inflammation may drive SWA.
EEG connectivity analyses
To address whether integration also fades in delirium, we
measured functional connectivity using PLI.20 We hypoth-
esised that, whilst local SWA in frontal cortex was insufficient
to cause delirium, when SWA transitioned to be global, the
ensuing reduction in cortical connectivity precipitated
delirium. First, we confirmed that alpha band was the appro-
priate frequency range to explore in our data (as suggested by a
prior study11) by plotting the PLI spectrum in 0.4883 Hz fre-
quency resolution. Indeed, there was a clear peak in connec-
tivity in the alpha range preoperatively (linear mixed-effects
model across delirium states and pre-/postoperation Pal-
pha<0.0001; Fig. 4a). Delirium was also associated with an in-
crease in Fz-Pz connectivity in the delta range (Fig. 4a).
10 - Tanabe et al.
To make our analysis sensitive to change in the non-
delirious group (where we observed increases in SWA post-
operatively), we placed a connectivity seed in frontal regions
(see Supplementary Fig. 1 for methodological description) and
calculated connectivity with other scalp regions. In case-
control analyses (Fig. 4b rows), preoperatively, patients who
subsequently became delirious showed increased frontal
connectivity. Postoperatively, however, they showed
decreased connectivity.
Change in connectivity from preoperative levels
We next analysed the change in connectivity from preoperative
to postoperative state across groups. In the non-delirious
subjects, there was no change in connectivity from the pre-
operative period, consistent with only localised SWA (Fig. 4b,
columns). However, the transition into delirium was associ-
ated with significant decreases in frontal connectivity with
posterior brain regions (Fig. 4c). Of delirious subjects, 19
showed decreases in Fz-Pz alpha PLI and three showed in-
creases (Supplementary Fig. 9).
Connectivity sensitivity analyses
The results without outlier rejection are presented in
Supplementary Fig. 10. We confirmed changes of connectivity
that correlated with DRS with calculations of pairwise con-
nectivity between all electrodes and a conservative FDR
correction across pairwise connections (Supplementary
Fig. 11). These data emphasised the correlations of fronto-
temporal connections with delirium severity. In sum, our data
suggest that, in delirium, as SWA extends to reach posterior
brain regions, there is an associated breakdown in brain
connectivity.
Possible mechanistic associations of the change inconnectivity
Changes in connectivity were also correlated with SWA
(r2¼0.257; P<0.0001), DRS (r2¼0.195; P<0.001), IL-10 (r2¼0.152;
P¼0.008), and MCP-1 (r2¼0.253; P<0.001; Fig. 4d).
Post hoc investigation into preoperative structuralconnectivity and delirium
One aspect of these connectivity observations is particularly at
odds with our published hypothesis of delirium.7 Preopera-
tively, subjects who would later become delirious had higher
EEG functional connectivity than subjects who did not become
delirious. Prima facie, this observation also seemed to contra-
dict extensive prior data showing impaired structural con-
nectivity before delirium; see for example Cavallari and
colleagues.27 Therefore, we analysed available structural
connectivity using preoperative DTI. Consistent with prior
data,27 preoperatively, patients before delirium had impaired
structural connectivity, reflected by increased RD, adjusted for
age and gender as detected using TBSS in FSL (voxel-wise
statistics: number of voxels¼4260, FWE P¼0.047, t¼4.5; mean
statistics: RDdelirium>RDnon-delirium with Wilcoxon rank-sum
test; P<0.001; Fig. 5a; Supplementary Table 3). Again, similar
to prior results,27 increased preoperative RD values also
correlated with increasing postoperative delirium severity,
adjusted for age and gender (voxel-wise statistics: number of
voxels¼5595, FWE P¼0.044, t¼5.23; mean statistics: association
of mean RD in significant voxels and delirium severity was
r2¼0.29, P<0.001; Fig. 5b). Similar findings were observed in MD
as well, when adjusted for age and gender (delirium incidence:
voxel-wise statistics: number of voxels¼4757, FWE P¼0.026,
t¼5.33; mean statistics: mean statistics: MDdelirium>MDnon-
delirium with Wilcoxon rank-sum test, P<0.001; delirium severity:
voxel-wise statistics: number of voxels¼3747, FWE P¼0.036,
t¼4.41; mean statistics: association of mean MD in significant
voxels and delirium severity was r2¼0.2, P<0.001;Supplementary Fig. 12; Supplementary Table 4). Associations
with AD and FA were not identified (data not shown).
Post hoc investigation into preoperative structuralconnectivity and EEG functional connectivity
We hypothesised that increased functional connectivity in the
EEG may represent a mechanism of compensation for under-
lying structural pathology based on recent hypotheses from
neuroimaging.31 Next, we quantified the mean value of RD
across voxels that correlated with delirium severity, and
looked for how these correlated with the preoperative EEG
connectivity measures. To do this, we correlated the measure
with topographic EEG connectivity, testing whether the func-
tional connectivity changes in the EEG reflected a compensa-
tory response to the underlying structural pathology. Positive
correlations were noted, focused on left frontal regions, for the
relationship of RD and alpha band frontal connectivity (elec-
trode Fz r2¼0.491; P¼0.0012; Fig. 5c). These data suggest that, as
structural connectivity worsened (higher RD) on the right,
functional connectivity of the EEG increased on the left, sup-
porting the concept that increased preoperative functional
connectivity is a compensatory mechanism for underlying
structural neurodegeneration.
Discussion
Our data suggest that local frontal SWA can occur post-
operatively, but does not result in delirium. Rather, post-
operative delirium results when inflammation-driven SWA
extends to involve occipitoparietal cortex associated with a
breakdown in connectivity. Our prior hypothesis7 emphasised
the role of connectivity in delirium; a subsequent study sup-
ported this idea,11 but did not relate the changes mechanisti-
cally to SWA, inflammation, or investigate proportionality to
delirium severity. That study was also limited by its case-
control design. We have shown clear links to inflammatory
models of delirium through correlation of contemporaneous
changes in systemic cytokines, and relate the connectivity
changes to SWA. Whilst we are presently unable to manipu-
late delirium experimentally to test causal mechanisms, our
data are strongly supported by several Bradford Hill criteria for
causality: temporal sequence, strength of change, and dose
dependence. Our data also show coherence with the dementia
literature32e36 and biological plausibility based on both the links
between inflammation and delirium,37 and also the changes in
SWA following sleep deprivation and consequent impair-
ments in cognition.19,29
An unexpected finding was that of increased frontal high-
frequency power and alpha band connectivity before
delirium. We speculate that these changes were compensa-
tory responses to underlying neurodegeneration, and provided
evidence for this from structural imaging data. Increased
frontal alpha power has recently been identified as a signature
of amyloid disease.38 As an extension of recent hypotheses
Neural correlates of delirium - 11
from neuroimaging,31 we surmise that these electrophysio-
logical changes may represent evidence of functional com-
pensations whereby increased network connectivity is
recruited as a mechanism tomaintain cognitive function from
chronic neurodegenerative pathologies. Interestingly, the
non-delirious subjects showed an increase in frontal alpha
power and maintained cognitive function postoperatively.
Increased alpha activity and connectivity may be a key
compensatory mechanism to maintain cognitive function in
the presence of a physiological stressor (such as inflamma-
tion). Increasing 8 Hz frontotemporal connectivity (within our
alpha range) has recently been shown to improve cognitive
performance in the older population.39We have replicated and
extended prior work10,11 showing that decreases in alpha band
connectivity may contribute to the cognitive dysfunction in
delirium, although it is important to note that decreases in
alpha band connectivity did not occur in all delirious subjects.
It is presently unclear whether these subjects showed con-
nectivity changes in other bands leading to delirium, or
whether connectivity changes do not contribute to delirium in
these subjects. Nonetheless, manipulation of alpha band
connectivity may yet prove to be a therapy for delirium in at
least some subjects.
We note some important limitations of our study. Firstly,
the cohort was of modest size, and it may be that more diverse
changes may be identified in a larger cohort, or alternative
changes may occur in other types of delirium, for example,
those induced by medications. We acknowledge these limita-
tions, but stress that we have likely identified the strongest
relationships, which are most likely to be causal, and that
inflammation is a very common mechanism of delirium6 (as
delirium by definition arises from a physiological stressor).
Nonetheless, our focus on inflammation does not imply that
the associations we have discovered will extend to other
clinical settings or mechanistic types of delirium, where pa-
thologies other than inflammation may play a larger role.
Secondly, it is not possible to perform more invasive electro-
physiological studies in most types of delirium. Thirdly, it is
possible that some form of unmeasured confounding may still
affect our results; however, we control for the baseline state
and calculated changes in the perioperative period. This
approach, essentially normalising to the baseline state, ad-
justs for many of the confounds of the baseline state,
including age and co-morbidities. This is critical, given we
have observed preoperative differences in the EEG. We also
conducted sensitivity analyses for cohort type (IPOD-B2 vs
IPOD-B3) and exposure to sedative medications.
In summary, our data show that changes in occipitoparietal
cortical SWA correlated with worsening delirium severity,
systemic inflammation, and impaired connectivity. Hence,
whilst frontal, local SWA occurs in postoperative patients,
delirium results when SWA progresses to involve posterior
brain regions, with an associated reduction in connectivity.
Authors’ contributions
Study design: RDS, MIB
Data collection/analysis: RDS, ST, HL, CC, ZF, TB, RM
Devising of imaging protocol: VP
Imaging analyses: RM, VP
EEG analyses: ST, RDS, MIB
Statistical advice: BK
Writing of paper: RDS, ST
Declaration of interest
All authors declare no competing interests that may be rele-
vant to the submitted work.
Funding
National Institutes of Health (K23 AG055700) to RDS; National
Institutes of Health (R01 AG063849-01) to RDS; National Heart,
Lung, and Blood Institute (5T32HL091816-07) to HL.
Acknowledgements
The authors thank Drs Brady Riedner and Giulio Tononi for
advice and loan of EEG equipment.
Appendix A. Supplementary data
Supplementary data to this article can be found online at
https://doi.org/10.1016/j.bja.2020.02.027.
References
1. Inouye SK, Westendorp RG, Saczynski JS. Delirium in
elderly people. Lancet 2014; 383: 911e22
2. Witlox J, Eurelings LS, de Jonghe JF, Kalisvaart KJ,
Eikelenboom P, van Gool WA. Delirium in elderly patients
and the risk of postdischarge mortality, institutionaliza-
tion, and dementia: a meta-analysis. JAMA 2010; 304:
443e51
3. Leslie DL, Marcantonio ER, Zhang Y, Leo-Summers L,
Inouye SK. One-year health care costs associated with
delirium in the elderly population. Arch Intern Med 2008;
168: 27e32
4. Hshieh TT, Fong TG, Marcantonio ER, Inouye SK. Cholin-
ergic deficiency hypothesis in delirium: a synthesis of
current evidence. J Gerontol A Biol Sci Med Sci 2008; 63:
764e72
5. Cerejeira J, Firmino H, Vaz-Serra A, Mukaetova-
Ladinska EB. The neuroinflammatory hypothesis of
delirium. Acta Neuropathol 2010; 119: 737e54
6. Cunningham C, Maclullich AM. At the extreme end of the
psychoneuroimmunological spectrum: delirium as a
maladaptive sickness behaviour response. Brain Behav
Immun 2013; 28: 1e13
7. Sanders RD. Hypothesis for the pathophysiology of
delirium: role of baseline brain network connectivity and
changes in inhibitory tone. Med Hypotheses 2011; 77: 140e3
8. Tononi G. An information integration theory of con-
sciousness. BMC Neurosci 2004; 5: 42
9. Bastos AM, Usrey WM, Adams RA, Mangun GR, Fries P,
Friston KJ. Canonical microcircuits for predictive coding.
Neuron 2012; 76: 695e711
10. Numan T, Slooter AJC, van der Kooi AW, et al. Functional
connectivity and network analysis during hypoactive
delirium and recovery from anesthesia. Clin Neurophysiol
2017; 128: 914e24
11. van Dellen E, van der Kooi AW, Numan T, et al. Decreased
functional connectivity and disturbed directionality of
information flow in the electroencephalography of
intensive care unit patients with delirium after cardiac
surgery. Anesthesiology 2014; 121: 328e35
12 - Tanabe et al.
12. Murphy M, Riedner BA, Huber R, Massimini M, Ferrarelli F,
Tononi G. Source modeling sleep slow waves. Proc Natl
Acad Sci U S A 2009; 106: 1608e13
13. Murphy M, Bruno MA, Riedner BA, et al. Propofol anes-
thesia and sleep: a high-density EEG study. Sleep 2011; 34:
283e91
14. Ponten SC, Tewarie P, Slooter AJ, Stam CJ, van Dellen E.
Neural network modeling of EEG patterns in encepha-
lopathy. J Clin Neurophysiol 2013; 30: 545e52
15. Inouye SK, van Dyck CH, Alessi CA, Balkin S, Siegal AP,
Horwitz RI. Clarifying confusion: the confusion assess-
ment method. A new method for detection of delirium.
Ann Intern Med 1990; 113: 941e8
16. Marcantonio ER, Ngo LH, O’Connor M, et al. 3D-CAM:
derivation and validation of a 3-minute diagnostic inter-
view for CAM-defined delirium: a cross-sectional diag-
nostic test study. Ann Intern Med 2014; 161: 554e61
17. Ely EW, Inouye SK, Bernard GR, et al. Delirium in me-
chanically ventilated patients: validity and reliability of
the confusion assessment method for the intensive care
unit (CAM-ICU). JAMA 2001; 286: 2703e10
18. Trzepacz PT, Mittal D, Torres R, Kanary K, Norton J,
Jimerson N. Validation of the Delirium Rating Scale-
revised-98: comparison with the delirium rating scale
and the cognitive test for delirium. J Neuropsychiatry Clin
Neurosci 2001; 13: 229e42
19. Nir Y, Andrillon T, Marmelshtein A, et al. Selective
neuronal lapses precede human cognitive lapses
following sleep deprivation. Nat Med 2017; 23: 1474e80
20. Vinck M, Oostenveld R, van Wingerden M, Battaglia F,
Pennartz CM. An improved index of phase-
synchronization for electrophysiological data in the
presence of volume-conduction, noise and sample-size
bias. Neuroimage 2011; 55: 1548e65
21. Smith SM, Nichols TE. Threshold-free cluster enhance-
ment: addressing problems of smoothing, threshold
dependence and localisation in cluster inference. Neuro-
image 2009; 44: 83e98
22. Neter J, Kutner MH, Nachtsheim CJ, Wasserman W.
Applied linear statistical models. Chicago, IL: McGraw-Hill;
1996
23. Andersson JLR, Sotiropoulos SN. An integrated approach
to correction for off-resonance effects and subject move-
ment in diffusion MR imaging. Neuroimage 2016; 125:
1063e78
24. Smith SM, Jenkinson M, Woolrich MW, et al. Advances in
functional and structural MR image analysis and imple-
mentation as FSL. Neuroimage 2004; 23: S208e19
25. Avants BB, Tustison NJ, Song G, Cook PA, Klein A, Gee JC.
A reproducible evaluation of ANTs similarity metric per-
formance in brain image registration. Neuroimage 2011; 54:
2033e44
26. Schwarz CG, Gunter JL, Ward CP, et al. The Mayo clinic
adult life span template: better quantification across the
life span. Alzheimers Dement 2017; 13: P93e4
27. Cavallari M, Dai W, Guttmann CR, et al. Neural substrates
of vulnerability to postsurgical delirium as revealed by
presurgical diffusion MRI. Brain 2016; 139: 1282e94
28. Smith SM, Jenkinson M, Johansen-Berg H, et al. Tract-
based spatial statistics: voxelwise analysis of multi-
subject diffusion data. Neuroimage 2006; 31: 1487e505
29. Vyazovskiy VV, Olcese U, Hanlon EC, Nir Y, Cirelli C,
Tononi G. Local sleep in awake rats. Nature 2011; 472:
443e7
30. van den Boogaard M, Kox M, Quinn KL, et al. Biomarkers
associated with delirium in critically ill patients and their
relation with long-term subjective cognitive dysfunction;
indications for different pathways governing delirium in
inflamed and noninflamed patients. Crit Care 2011; 15:
R297
31. Sala-Llonch R, Bartres-Faz D, Junque C. Reorganization of
brain networks in aging: a review of functional connec-
tivity studies. Front Psychol 2015; 6: 663
32. Babiloni C, Binetti G, Cassetta E, et al. Sources of cortical
rhythms change as a function of cognitive impairment in
pathological aging: a multicenter study. Clin Neurophysiol
2006; 117: 252e68
33. Babiloni C, Del Percio C, Lizio R, et al. Abnormalities of
resting state cortical EEG rhythms in subjects with mild
cognitive impairment due to Alzheimer’s and Lewy body
diseases. J Alzheimers Dis 2018; 62: 247e68
34. Gianotti LR, Kunig G, Lehmann D, et al. Correlation be-
tween disease severity and brain electric LORETA to-
mography in Alzheimer’s disease. Clin Neurophysiol 2007;
118: 186e96
35. Stam CJ, de Haan W, Daffertshofer A, et al. Graph theo-
retical analysis of magnetoencephalographic functional
connectivity in Alzheimer’s disease. Brain 2009; 132:
213e24
36. Engels MM, Stam CJ, van der Flier WM, Scheltens P, de
Waal H, van Straaten EC. Declining functional connec-
tivity and changing hub locations in Alzheimer’s disease:
an EEG study. BMC Neurol 2015; 15: 145
37. Cape E, Hall RJ, van Munster BC, et al. Cerebrospinal fluid
markers of neuroinflammation in delirium: a role for
interleukin-1beta in delirium after hip fracture.
J Psychosom Res 2014; 77: 219e25
38. Nakamura A, Cuesta P, Fernandez A, et al. Electromag-
netic signatures of the preclinical and prodromal stages of
Alzheimer’s disease. Brain 2018; 141: 1470e85
39. Reinhart RMG, Nguyen JA. Working memory revived in
older adults by synchronizing rhythmic brain circuits. Nat
Neurosci 2019; 22: 820e7
Handling editor: Michael Avidan